Abstract: An input driven self-clocked dynamic comparator, and associated systems and methods are described herein. In one embodiment, self-clocked dynamic comparator, includes a latch configured to receive an input voltage (VIN), a reference voltage (VREF) and a clocking (CLKsf) signal, and configured to output a first rail-to-rail output (OUT+) signal and a second rail-to-rail output (OUT?) signal. The self-clocked dynamic comparator also includes a pre-amplifier (PRE-AMP) configured to output an enable (TRI) signal based on a comparison between the VIN and an adjusted VREF. The self-clocked dynamic comparator further includes a pre-amplifier (PRE-AMP) configured to output an enable (TRI) signal based on a comparison between the VIN and an adjusted VREF, and a logic gate configured to receive the TRI signal and one of the OUT+ signal and OUT? signal, and configured to output the CLKsf signal. The cycles of the CLKsf signal cause the latch to dissipate energy.

Abstract: An input driven self-clocked dynamic comparator, and associated systems and methods are described herein. In one embodiment, self-clocked dynamic comparator, includes a latch configured to receive an input voltage (VIN), a reference voltage (VREF) and a clocking (CLKsf) signal, and configured to output a first rail-to-rail output (OUT+) signal and a second rail-to-rail output (OUT?) signal. The self-clocked dynamic comparator also includes a pre-amplifier (PRE-AMP) configured to output an enable (TRI) signal based on a comparison between the VIN and an adjusted VREF. The self-clocked dynamic comparator further includes a pre-amplifier (PRE-AMP) configured to output an enable (TRI) signal based on a comparison between the VIN and an adjusted VREF, and a logic gate configured to receive the TRI signal and one of the OUT+ signal and OUT? signal, and configured to output the CLKsf signal. The cycles of the CLKsf signal cause the latch to dissipate energy.

Abstract: The invention disclosed herein is directed to scintillation detectors capable of detecting the position or depth of gamma photon interactions occurring within a scintillator, thereby improving the resolution of ring based positron emission tomography (PET) imaging systems. In one embodiment, the invention is directed to a scintillation detector that comprises at least one pair of side-by-side conjunct scintillation crystal bars having a shared interface between, and a solid-state semiconductor photodetector optically coupled to each output window of each individual scintillation crystal bar. The solid-state semiconductor photodetector includes an array of discrete sensitive areas disposed across a top surface of a common substrate, wherein each sensitive area contains an array of discrete micro-pixelated avalanche photodiodes, and wherein the output window of each scintillation crystal bar is optically coupled to each respective sensitive area in a one-on-one relationship.

Abstract: The invention disclosed herein is directed to scintillation detectors capable of detecting the position or depth of gamma photon interactions occurring within a scintillator, thereby improving the resolution of ring based positron emission tomography (PET) imaging systems. In one embodiment, the invention is directed to a scintillation detector that comprises at least one pair of side-by-side conjunct scintillation crystal bars having a shared interface between, and a solid-state semiconductor photodetector optically coupled to each output window of each individual scintillation crystal bar. The solid-state semiconductor photodetector includes an array of discrete sensitive areas disposed across a top surface of a common substrate, wherein each sensitive area contains an array of discrete micro-pixelated avalanche photodiodes, and wherein the output window of each scintillation crystal bar is optically coupled to each respective sensitive area in a one-on-one relationship.

Abstract: A method is disclosed for obtaining linear attenuation coefficients for interpreting a PET scan of a region. The method is suitable for use when high molecular weight materials are present in the region, such as contrast agents or metal objects. The method includes obtaining first and second x-ray CT data sets of the region of interest at two different energies or voltage potentials and differencing corresponding CT numbers. The difference values are used to distinguish portions of the region that are bone from portions of the region that are contrast agent or other high molecular weight material. The obtained CT data set is then used to obtain an attenuation coefficient map of the region at the PET energy of 511 keV, for example, using a linear scaling factor suited to the particular identified material. Difference values at or near zero may be used to identify soft tissue portions of the region.